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    Anoverviewofnickeltitaniumalloysused Anoverviewofnickeltitaniumalloysused Document Transcript

    • IEJ339.fm Page 297 Saturday, June 10, 2000 8:50 AM REVIEW Blackwell Science, Ltd An overview of nickel–titanium alloys used in dentistry S. A. Thompson Department of Adult Dental Health, University of Wales College of Medicine, Cardiff, UK Abstract their original shape following deformation. These prop- erties are of interest in endodontology as they allow Thompson SA. An overview of nickel–titanium alloys used in construction of root canal instruments that utilize these dentistry. International Endodontic Journal, 33, 297–310, 2000. favourable characteristics to provide an advantage Literature review The nickel–titanium alloy Nitinol when preparing curved canals. This review aims to pro- has been used in the manufacture of endodontic instru- vide an overview of Nitinol alloys used in dentistry in ments in recent years. Nitinol alloys have greater order for its unique characteristics to be appreciated. strength and a lower modulus of elasticity compared Keywords: endodontics, nickel–titanium, root canals. with stainless steel alloys. The super-elastic behaviour of Nitinol wires means that on unloading they return to Received 13 October 1999; accepted 7 December 1999 Introduction As the alloy has greater strength and a lower modulus of elasticity compared with stainless steel (Andreasen In the early 1960s, a nickel–titanium alloy was & Morrow 1978, Andreasen et al. 1985, Walia et al. 1988), developed by W. F. Buehler, a metallurgist investigating there may be an advantage in the use of NiTi instru- nonmagnetic, salt resisting, waterproof alloys for the ments during the preparation of curved root canals, space programme at the Naval Ordnance Laboratory because the files will not be permanently deformed in Silver Springs, Maryland, USA (Buehler et al. 1963). as easily as would happen with traditional alloys The thermodynamic properties of this intermetallic (Schäfer 1997). alloy were found to be capable of producing a shape memory effect when specific, controlled heat treat- ment was undertaken (Buehler et al. 1963). The alloy was Metallurgy of nickel–titanium alloys named Nitinol, an acronym for the elements from The nickel–titanium alloys used in root canal treatment which the material was composed; ni for nickel, ti contain approximately 56% (wt) nickel and 44% (wt) for titanium and nol from the Naval Ordnance Labor- titanium. In some NiTi alloys, a small percentage (<2% atory. Nitinol is the name given to a family of inter- wt) of nickel can be substituted by cobalt. The resultant metallic alloys of nickel and titanium which have been combination is a one-to-one atomic ratio (equiatomic) found to have unique properties of shape memory of the major components and, as with other metallic and super-elasticity. systems, the alloy can exist in various crystallographic The super-elastic behaviour of Nitinol wires means forms (Fig. 1). The generic term for these alloys is 55- that on unloading they return to their original shape Nitinol; they have an inherent ability to alter their type before deformation (Lee et al. 1988, Serene et al. 1995). of atomic bonding which causes unique and signi- ficant changes in the mechanical properties and crystallographic arrangement of the alloy. These Correspondence: Dr Shelagh Thompson, Department of Adult changes occur as a function of temperature and stress. Dental Health, University of Wales College of Medicine, Heath Park, Cardiff CF14 4XY, Wales, UK (fax: +44 (0)2920 742479; e-mail: The two unique features that are of relevance to thompsonsa@cardiff.ac.uk). clinical dentistry occur as a result of the austenite to © 2000 Blackwell Science Ltd International Endodontic Journal, 33, 297–310, 2000 297
    • IEJ339.fm Page 298 Saturday, June 10, 2000 8:50 AM Overview of NiTi alloys Thompson Figure 3 Diagrammatic representation of the super-elasticity effect of NiTi alloy. that when it is cooled through a critical transformation temperature range (TTR), the alloy shows dramatic changes in its modulus of elasticity (stiffness), yield strength and electric resistivity as a result of changes in electron bonding. By reducing or cooling the temperature Figure 1 Diagrammatic representation of the martensitic through this range, there is a change in the crystal transformation and shape memory effect of NiTi alloy. structure which is known as the martensitic transformation; the amount of this transformation is a function of the start (Ms) and finish (Mf ) temperature. The phenomenon causes a change in the physical properties of the alloy (Wang et al. 1972) and gives rise to the shape memory characteristic. The hysteresis of the martensitic trans- formation is shown in Fig. 4. The transformation induced in the alloy occurs by a shear type of process to a phase called the martensitic or daughter phase (Fig. 1), which gives rise to twinned martensite (Fig. 1) that forms the structure of a closely packed hexagonal lattice (Fig. 1). Almost no macro- scopic shape change is detectable on the transformation, unless there is application of an external force. The martensite shape can be deformed easily to a single orientation by a process known as de-twinning to de- twinned martensite, when there is a ‘flipping over’ type of shear. The NiTi alloy is more ductile in the martens- Figure 2 Diagrammatic representation of the shape memory itic phase than the austenite phase. The martensitic effect of NiTi alloy. transformation and the shape memory effect is shown in Fig. 1. The deformation can be reversed by heating the alloy above the TTR (reverse transformation temperature martensite transition in the NiTi alloy; these charac- range or RTTR) with the result that the properties of the teristics are termed shape memory and super-elasticity NiTi alloy revert back to their previous higher temperature (Figs 2 and 3). values (Fig. 1). The alloy resumes the original parent structure and orientation as the body-centred cubic, high temperature phase termed austenite with a stable Structure of nickel–titanium energy condition (Fig. 1). The total atomic movement The crystal structure of NiTi alloy at high temperature between adjacent planes of atoms is less than a full ranges (100 °C) is a stable, body-centred cubic lattice interatomic distance when based on normal atomic which is referred to as the austenite phase or parent lattice arrangements. This phenomenon is termed shape phase (Fig. 1). Nitinol has the particular characteristic memory (Fig. 2) and allows the alloy to return to its 298 International Endodontic Journal, 33, 297–310, 2000 © 2000 Blackwell Science Ltd
    • IEJ339.fm Page 299 Saturday, June 10, 2000 8:50 AM Thompson Overview of NiTi alloys Figure 4 Hysteresis of martensitic transformation. previous shape, by forming strong, directional and thus lowering the total number of bonding electrons. energetic electron bonds to pull back displaced atoms to However, formation of a detrimental second phase their previous positions; the effect of this transforma- NiTi3 occurs if excess nickel is added in attempts to tion is instantaneous. lower the TTR. It is possible using the shape memory effect to educate or place the NiTi alloy into a given configuration at a Stress-induced martensitic transformation given temperature. This can be carried out at lower temperatures which deform the NiTi with a very low The transition from the austensitic to martensitic phase force and results in the ‘twins’ all occurring in the can also occur as a result of the application of stress, same direction. When the NiTi is heated through its such as occurs during root canal preparation. In most transformation temperature it will recover its original metals, when an external force exceeds a given amount ‘permanent’ shape (Fig. 2). The application of shape mechanical slip is induced within the lattice causing memory to orthodontics is discussed later. In terms of permanent deformation; however, with NiTi alloys a endodontology, this phenomenon may translate to the stress-induced martensitic transformation occurs, rather ability to remove any deformation within nickel– than slip. This causes: titanium instruments by heating them above 125 °C • a volumetric change associated with the transition (Serene et al. 1995). from one phase to the other and an orientation The transition temperature range for each nominal relation is developed between the phases 55-Nitinol alloy depends upon its composition, as this • the rate of the increase in stress to level off due to causes considerable variability in the number of electrons progressive deformation (Fig. 5) even if strain is available for bonding to occur and is constant for a par- added due to the martensitic transformation. This ticular NiTi alloy composition. The TTR of a 1 : 1 ratio results in the so-called super-elasticity (Fig. 4), a of nickel and titanium is in the range of –50 to +100 °C. movement which is similar to slip deformation. The Reduction in the TTR can be achieved in several ways; differences between the tensile behaviours of NiTi in the manufacturing process both cold working and and stainless steel alloy can be seen in Fig. 6. thermal treatment can significantly affect TTR, as • springback when the stress decreases or stops can altering the nickel : titanium ratio in favour of without permanent deformation occurring (Fig. 3). excess nickel or by substituting cobalt for nickel, atom Springback is defined as load per change in deflec- for atom. Cobalt substitution produces alloys with tion (Andreasen & Morrow 1978), to the previous the composition NiTixCo1-x. The TTR can be lowered shape with a return to the austenite phase, pro- progressively by continued substitution of cobalt for vided the temperature is within a specific range nickel as cobalt possesses one less electron than nickel, (Fig. 4). © 2000 Blackwell Science Ltd International Endodontic Journal, 33, 297–310, 2000 299
    • IEJ339.fm Page 300 Saturday, June 10, 2000 8:50 AM Overview of NiTi alloys Thompson Figure 5 NiTi phase transformation. Figure 6 Diagrammatic representation of the tensile behaviour of stainless steel and NiTi super-elastic alloy and mechanisms of elastic deformation. The plastic deformation that occurs in NiTi alloys range (SRTR). This has also been termed ‘mechanical within or below the TTR is recoverable, within certain memory’ (Buehler & Wang 1968). This is unlike conven- limits, on reverse transformation. It is this phenome- tional metallic stress-strain behaviour where elastic non of crystalline change which gives rise to the response in conventional alloys is recoverable, but is shape memory effect of the material and the super- small in size; and where larger strains are associated elastic behaviour. The part of the RTTR in which ‘shape with plastic deformation, that is not recoverable recovery’ occurs is termed the shape recovery temperature (Fig. 7). 300 International Endodontic Journal, 33, 297–310, 2000 © 2000 Blackwell Science Ltd
    • IEJ339.fm Page 301 Saturday, June 10, 2000 8:50 AM Thompson Overview of NiTi alloys Figure 7 NiTi strength curve. Figure 8 Stress-strain curve: stainless steel and nickel–titanium. The super-elasticity of nickel–titanium allows deforma- metals which can occur in all possible combinations. As tions of as much as 8% strain to be fully recoverable such, a second group of Nitinol alloys can be formed if (Fig. 8), in comparison with a maximum of less than the NiTi alloy contains more nickel and as this approaches 1% with other alloys, such as stainless steel. Although 60% (wt) Ni an alloy known as 60-Nitinol forms. The other alloys such as copper–zinc, copper–aluminium, shape memory effect of this alloy is lower, although gold– cadmium and nickel–niobium have been found to its ability to be heat-treated increases. Both 55 and 60- have super-elastic properties (Buehler & Wang 1968), Nitinols are more resilient, tougher and have a lower nickel–titanium is the most biocompatible material and modulus of elasticity than other alloys such as stainless has excellent resistance to corrosion. steel, Ni–Cr or Co–Cr (Fig. 8). Table 1 shows the values An alloy system is an aggregate of two or more for typical properties of Nitinol alloys. © 2000 Blackwell Science Ltd International Endodontic Journal, 33, 297–310, 2000 301
    • IEJ339.fm Page 302 Saturday, June 10, 2000 8:50 AM Overview of NiTi alloys Thompson Table 1 Typical properties of Nitinol 55-Nitinol 55-Nitinol alloys Property austenite martensite Physical Density (gm cm3) 6.45 Melting point (°C) 1310 Magnetic permeability <1.002 Coefficient of thermal expansion (× 106/°C) 11.0 6.6 Electrical resistivity (ohm-cm) 100 × 10 −6 80 × 10 −6 Hardness 950 °C (Furnace cooled) 89 RB Hardness 950 °C (Quenched-R.T. water) 89 RB Mechanical Young’s modulus (Gpa) 120 50 Yield strength (Mpa) 379 138 Ultimate tensile strength (Mpa) 690–1380 Elongation 13–40% Shape memory Transformation temperature (°C) –50 to +100 Latent heat of transformation 10.4 BTU lb–1 Shape memory recoverable strain 6.5–8.5% Super-elastic recoverable strain up to 8% Transformation fatigue life several hundred at 6% strain cycles at 2% strain 105cycles at 0.5% strain 107cycles Figure 9 Diagrammatic representation of the manufacturing process of Nitinol alloy. 1968). One of the problems encountered with arc-melting Manufacture of Nitinol alloy was that it required multiple remelts to ensure chemical Nickel–titanium alloy production is a very complex homogeneity; however, importantly this process pro- process that consists of: duces only minimum contamination of the alloy. Current • vacuum melting/casting manufacture involves the use of vacuum induction • press forging melting in graphite crucibles (Fig. 9) that ensures effective • rotary swaging alloy mixing by simple means, with slight carbon con- • rod/wire rolling tamination in the melt forming TiC (Buehler & Cross In the past, NiTi alloys with near stoichiometric 1969). The presence of oxide impurities does not effect composition have been produced satisfactorily by both the unique properties of 55-Nitinol, as these appear to arc and induction melting methods (Buehler & Wang be evenly distributed within the NiTi matrix. 302 International Endodontic Journal, 33, 297–310, 2000 © 2000 Blackwell Science Ltd
    • IEJ339.fm Page 303 Saturday, June 10, 2000 8:50 AM Thompson Overview of NiTi alloys The double vacuum melting manufacturing process ensures purity and quality and maintains the mechanical properties of the alloy. The raw materials are carefully formulated before the alloy is melted by vacuum induction. After this process, vacuum arc remelting takes place to improve the alloy chemistry, homogeneity and structure. The double melted ingots are hot worked and then cold worked to a variety of shapes and sizes according to product specifications, i.e. Nitinol wires, bars, etc. as described earlier. Alloys for orthodontic or medical use can be produced as drawn or with mechanically cleaned surfaces. Hot and cold working can be undertaken on Nitinol alloys, below the crystallization temperature. The alloy Figure 10 SEM photomicrograph of milling marks and roll- composition is important to the manufacturing process over on a rotary NiTi instrument. and it appears that 55-Nitinol can be processed by all forms of hot working more easily than 60-Nitinol. Strengthening of the alloy occurs through low temper- ature deformation and maintains a minimum of 12% deformation. Attempts to twist instruments in a con- tensile elongation. Some NiTi alloys appear to be sensitive ventional way would probably result in instrument to the effects of heat treatment that can effect both shape fracture (Schäfer 1997). The instrument profile (design) memory and the pseudo-elastic behaviour; however, has to be ground into the Nitinol blanks. Further NiTi alloys of near stoichiometric composition such difficulties during production include elimination of as are used in dentistry do not appear to be affected surface irregularities (milling marks) and metal flash (Saburi et al. 1982, Mercier & Torok 1982). (roll-over) on the cutting edges that may compromise Gould (1963) studied the machining characteristics the cutting ability of these instruments and potentially of nickel–titanium alloys and found that tool wear was cause problems with corrosion (Fig. 10). rapid and the cutting speed, feed, tool material, tool The composition of Nitinol used to construct endo- geometry and type of cutting fluid had an effect on the dontic instruments is 56% (wt) nickel and 44% (wt) results of the manufactured Nitinol. Specifically, these titanium. Although only one manufacturer (Dentsply, alloys could be turned 10 – 20 times faster with carbide Maillefer Instruments SA, Ballaigues, Switzerland) has tools than with high speed steel tools. Light feeds of released the absolute composition and manufacturing 0.003 – 0.005 in rev−1 are recommended in turning details of the nickel–titanium used to construct their Gould 1963) and in order to maximize the tool life, 55- instruments, it would appear that this is the only alloy Nitinol should be cut at a speed of 220 ft min–1. An composition that can utilize the super-elastic properties active highly chlorinated cutting oil is advised to obtain of the alloy. a reasonable drill-life along with the use of silicon It is possible to vary the composition of NiTi alloy in carbide wheels to grind the surface of Nitinol alloys. The order to give rise to wires with two different characteristics; speeds at which cutting tools should be operated vary either to be a super-elastic alloy or to have the shape according to the composition of the alloy. Therefore, it memory property. The differences between the alloys are appears that sharp carbide cutting tools are required to in their nickel content and the transitional temperature machine Nitinol alloys using techniques involving light range for the given alloy. Various parameters affect the feeds and slow speeds. transformation temperature; a decrease in the trans- formation temperature occurs with an increase in nickel content or by substituting trace elements such as cobalt Construction of root canal instruments as discussed previously, whilst an increase in annealing The manufacture of NiTi endodontic instruments is temperature increases the transformation temperature. more complex than that of stainless steel instruments, Ideally, for the manufacture of root canal instruments as the files have to be machined rather than twisted. the ultimate tensile strength of the alloy should be as The super-elasticity of the alloy means that it cannot high as possible to resist separation (Fig. 7), whilst the maintain a spiral as the alloy undergoes no permanent elongation parameters must be suitable for instrument © 2000 Blackwell Science Ltd International Endodontic Journal, 33, 297–310, 2000 303
    • IEJ339.fm Page 304 Saturday, June 10, 2000 8:50 AM Overview of NiTi alloys Thompson Figure 11 Diagrammatic representation of the production of finished Nitinol wire. flexibility, (Fig. 8) thereby decreasing canal transportation, ductivity and the mass of the material. The corrosion and to allow high resistance to fatigue. resistance of Nitinol alloys was evaluated by Buehler Once the alloy has been manufactured, it undergoes & Wang (1968) who reported that they performed various processes before the finished wire can be machined adequately in a marine environment. into a root canal instrument (Fig. 11). Essentially, the Duerig (1990) described applications for shape memory casting is forged in a press into a cylindrical shape prior NiTi alloys grouped according to the primary function of to rotary swaging under pressure, to create a drawn the memory element. An example of (i) free recovery was wire. The wire is then rolled to form a tapered shape with NiTi eyeglass frames, (ii) constrained recovery was couplings even pressure from a series of rollers applied to the wire. for joining aircraft hydraulic tubing and electrical con- During the construction phase, other processes are carried nectors, (iii) work production was actuators both electrical out on the rod-rolled wire including drawing the wire and thermal and (iv) super-elasticity was orthodontic onto a cone, annealing the wire in its coiled state, descal- archwire, guidewires and suture anchors. ing and further fine wire drawing followed by repeated Further uses of the super-elastic properties of NiTi annealing with the wire in a straight configuration. This wire were described by Stoeckel & Yu (1991). As super- stage is followed by drawing the actual profile or cross- elasticity is an isothermal event, applications with a well sectional shape of the wire, e.g. imparting either a round, controlled temperature environment are most successful, e.g. square or oblong shape prior to a cleaning and conditioning in the human body. NiTi wire has been used as ortho- process. The finished wire is stored on reels prior to dontic archwire and springs, in Mammalok® needle wire machining. This process is illustrated in Fig. 11. localizers (to locate and mark breast tumours), guidewires for catheters, suture needles and anchors, the temples and bridges for eyeglasses, and, in Japan, underwire brassieres. Uses of nickel–titanium alloy Nitinol wire was first used in the self-erectile action of a Use of nickel–titanium alloys in dentistry disc on rod antenna that recovered its prefolded shape above the transition temperature of the alloy (Buehler & Orthodontics Wang 1968). The unique ‘mechanical memory’ of 55- Nitinol allowed it to recover its original shape after Initially NiTi alloys were used in the construction of mechanical distortion by heating it above the transition orthodonic archwires. Extensive research published temperature. The rate of recovery of the antenna was in the materials science and orthodontic journals has determined by the rate at which the critical temperature allowed the properties of the material to be appreciated was reached, which depended on the thermal con- and used in an appropriate clinical manner. Many of 304 International Endodontic Journal, 33, 297–310, 2000 © 2000 Blackwell Science Ltd
    • IEJ339.fm Page 305 Saturday, June 10, 2000 8:50 AM Thompson Overview of NiTi alloys these studies have relevance to an understanding of work-hardening process, thus affecting the properties of NiTi alloys used in endodontology and a brief descrip- shape memory or super-elasticity. tion of this literature is described. Kusy & Stush (1987) observed a discrepancy between NiTi wires were first used in orthodontics by Andreasen the stated dimensions of wires of 10 Nitinol and seven beta & Hilleman (1971), who observed differences in the titanium wires; the sizes were smaller 95% of the time physical properties of Nitinol and stainless steel and neither wire obeyed simple yield strength relationships. orthodontic wires that allowed lighter forces to be used. The ultimate tensile strength of Nitinol wires increased The strength and resilience of NiTi wires meant there with decreasing cross-sectional area and also appeared was a reduction in the number of arch wire changes more ductile with increasing cross-sectional area. necessary to complete treatment. Rotations of teeth could Yoneyama et al. (1992) assessed the super-elasticity be accomplished in a shorter time, without increasing and thermal behaviour of 20 commercial NiTi ortho- patient discomfort. Nitinol wires showed better resistance dontic arch wires. A three-point bending test allowed to corrosion so were felt more appropriate for intraoral load-deflection curves to be determined and differential use than stainless steel. scanning calorimetry was used to determine thermal Andreasen & Morrow (1978) observed the unique behaviour due to phase transformation of the alloy. properties of Nitinol, including its outstanding elasticity Substantial differences were noted between the wires; (which allows it to be drawn into high-strength wires) some showed super-elasticity (which occurs with the and its ‘shape memory’ (which allows the wire when stress induced martensitic transformation), whilst other deformed, to ‘remember’ its shape and return to its original wires only had good springback qualities. Super-elasticity configuration). The most important benefits of Nitinol was only exhibited by wires showing high endothermic wire were its construction as a resilient, rectangular energy in the reverse transformation from the martensitic wire that allowed simultaneous rotation, levelling, tipping phase to the parent phase and with low load/deflection and torquing movements, to be accomplished early in ratios. These wires showed nearly constant forces in treatment. Limitations to the use of the material were the unloading process, a desirable physiological property noted, such as the time taken to bend the wires, the for orthodontic tooth movement; the lower the L/D ratio, necessity of not using sharp-cornered instruments that the less changeable is the force which the wire can display. could lead to breakage and the inability to be soldered or Clearly, there are differences in the mechanical welded to itself. Overall, the authors felt the material properties and thermal behaviour of NiTi alloy which represented a significant improvement over conventional vary with composition, machining characteristics and arch wire and was a valuable addition to the orthodontist’s differences in heat treatment during manufacture. The armamentarium. need for correct production of NiTi alloys was stressed Burstone & Goldberg (1980) observed beneficial by Yoneyama et al. (1992) in order that the desired characteristics such as low modulus of elasticity clinical characteristics could be obtained. combined with a high tensile strength that allowed Evans & Durning (1996) reported the differences in wires to sustain large elastic deflections due to the very formulations of nickel–titanium alloy and their applica- high springback quality. Limitations such as restricted tions in archwire technology. A review article published formability and the decrease of springback after bending by Kusy (1997) described the properties and characteristics prompted investigations into other alloys, such as beta of contemporary archwires from initial development titanium. Drake et al. (1982) concluded that Nitinol to their current use in variable modulus orthodontics wire was suitable mainly for pretorqued, preanglulated as advocated by Burstone (1981). The variation in brackets. composition of nickel–titanium alloys was discussed Miura et al. (1986) tested a new Japanese NiTi alloy together with the influence this had on the properties and compared it to stainless steel, Co–Cr–Ni and Nitinol of the resultant alloy. wires. Japanese NiTi alloy exhibited super-elastic properties and was least likely to undergo permanent deformation Corrosion behaviour of NiTi orthodontic wires during activation. The Nitinol wire showed less per- manent deformation and excellent springback qualities in The corrosion behaviour of Nitinol orthodontic wires comparison with the stainless steel and Co – Cr–Ni wires, was compared with stainless steel, cobalt-chrome and however, load and deflection were almost proportional, β-titanium by Sarkar et al. (1979). The wires were indicating lack of super-elastic qualities. This may have exposed to a 1% NaCl solution via an electrochemical been due to the fact that Nitinol was manufactured by a cyclic polarization technique. Scanning electron © 2000 Blackwell Science Ltd International Endodontic Journal, 33, 297–310, 2000 305
    • IEJ339.fm Page 306 Saturday, June 10, 2000 8:50 AM Overview of NiTi alloys Thompson microscopy and energy dispersive X-ray analysis was occurred on electrolytically corroded Nitinol wires, with used to determine differences between pre- and postpo- loosely bound corrosion products; however, after clinical larized surfaces. The Nitinol alloy was the only specimen use, no differences in surface characteristics were obvious to exhibit a pitting type corrosion attack, which the when comparing pre- and postoperative SEM photographs. authors concluded warranted further investigation. There was no significant difference between the surface Sarkar & Schwaninger (1980) studied the in vivo oxygen content of Nitinol compared to stainless steel, which corrosion characteristics of seven Nitinol wires in clinical would suggest that there were no differences in the clinical use for 3 weeks to 5 months. Scanning electron micros- performance of the two wires, in terms of corrosion. copy revealed the presence of numerous, round-bottomed, corrosion pits interspersed with corrosion products rich Effects of sterilization on NiTi orthodontic wires in titanium. This was presumed to be a mixed oxide of titanium and nickel. Fractured surfaces of Nitinol wires Mayhew & Kusy (1988) examined the effects of dry showed small equiaxed dimples that resulted from heat, formaldehyde-alcohol vapour and steam autoclave microvoid coalescence within the grain-boundary zones. sterilization on the mechanical properties and surface There appears to be correlation with in vitro (Sarkar topography of two different nickel–titanium arch wires. et al. 1979) and in vivo corrosion of Nitinol. The wires were being reused clinically, due to their high The performance of wires used in orthodontics can be cost. After sterilization, the elastic modulus and tensile affected by corrosion in the mouth. Edie & Andreasen properties were determined for Nitinol and Titanal wires (1980) examined Nitinol wires under SEM as received (Lancer Pacific, Carlsbad, CA, USA); laser scanning from the manufacturer and following 1 month to was employed to detect surface alterations caused by 1 year’s use in the mouth. They found no corrosion tarnish, corrosion or pitting. of the Nitinol wires with maintenance of a smooth, No detrimental effects were noted, and the nickel– undulating surface. In contrast, stainless steel wires titanium arch wires maintained their elastic properties, showed sharp elevations of metal particles on their surface. had excellent resilience and low load-deflection rates, Clinard et al. (1981) used polarization resistance and which led the authors to conclude that stabilized zero resistance ammetry to study the corrosion beha- martensitic alloys such as Nitinol could be heat sterilized, viour of stainless steel, cobalt– chromium, beta-titanium without forming tempered martensite. The specular and Nitinol orthodontic springs. They also studied the reflectivity for Nitinol was determined by laser spectros- effect of coupling the wires to stainless steel brackets. copy and ranged from 1.1 to 4.6 µ W. Sterilization did In orthodontic treatment, the corrosion behaviour of not appear to effect surface topography adversely. the wires was affected by coupling to the brackets. The load-deflection characteristics of NiTi wires after The effects of beta-titanium and cobalt–chromium were clinical recycling and dry heat sterilization were examined comparable showing less corrosion than the other by Kapila et al. (1992). Thirty 0.016 inch work-hardened wires, however, Nitinol was shown to be inferior to Nitinol and austensitic NiTi wires were subjected to a stainless steel, with a tendency to pitting attack. The three-point bending test in an ‘as received’ condition, authors concluded that over the relatively short period and after one and two cycles of dry heat sterilization for of orthodontic treatment, the effect of the corrosion did 5 min at temperatures that ranged from 203 to 217 °C. not appear to be deleterious to the mechanical pro- It was observed that recycling these wires after sterili- perties of the wires, and should not significantly effect zation causes significant changes to the loading and the outcome of treatment. unloading forces associated with the wires, together with To assess corrosion potential, Edie et al. (1981) com- a reduction in the pseudo-elasticity of NiTi wires and an pared Nitinol wire with stainless steel wire in clinical increase in the stiffness of both the Nitinol and NiTi wires. use for periods ranging from 1 to 8 months. Scanning Three types of nickel–titanium wires, a β-titanium electron microscopy was used to assess surface charac- and a stainless steel wire were sterilized by either cold, teristics; qualitative chemical information was obtained dry or steam autoclave sterilization by Smith et al. with X-ray spectrometry to indicate oxide prevalence (1992). A transverse load test, tensile strength and and organic contamination of the wires. Unused Nitinol corrosion resistance test was carried out on 40 wires wires exhibited large variations in surface texture with of each type used clinically for 1–6 months and on an undulating ‘bubbling’ or mottled ‘caked’ appearance In five wires in an as received condition. There were no comparison, stainless steel wires were generally smoother, clinically significant differences between the new or but showed small metallic prominences. Obvious pits previously used NiTi wires. 306 International Endodontic Journal, 33, 297–310, 2000 © 2000 Blackwell Science Ltd
    • IEJ339.fm Page 307 Saturday, June 10, 2000 8:50 AM Thompson Overview of NiTi alloys enhance the adhesiveness of nickel–titanium implants Other uses of nickel–titanium alloy in to bone was investigated by Kimura & Sohmura (1987) dentistry who sprayed the surface of both NiTi alloy and titanium alloy with Ti, by a plasma thermal spray under argon Castings for crowns and denture construction gas atmosphere. A pure Ti layer was formed after spraying, The use of NiTi alloy in the construction of dental however, a 5–10 µm crevice was noted between the prostheses was first investigated by Civjan et al. (1975) coated layer and the matrix metal and dissolution of the who cast 55-Nitinol into phosphate-bonded investment coated layer was detected when the material was placed moulds. However, castings of tensile bars, inlays and in 1% NaCl solution. crowns were found to be rough, brittle and devoid of It appeared that if the specimens were vacuum mechanical memory. The shape memory properties of annealed at 950 °C for 1–1.5 h the crevice disappeared, the alloy were investigated for construction of partial forming a bonded layer with a composition corresponding denture clasps. It proved difficult to adapt Nitinol wires to Ti2-Ni on the Ti-Ni matrix. Closer adhesion and to the cast, overbending was necessary and resilience corrosion resistance was achieved with the Ti specimen. was lost in fixing the shape; however, shape recovery Kimura & Sohmura (1987) felt that a thinner coating occurred within 2 – 5 s in the mouth and was improved of Ti or an application of Ti2-Ni alloy phase would be on further warming. worth investigating, to avoid the coated layer peeling Difficulties have been encountered in casting NiTi off when large strains were placed on the shape alloy using conventional dental casting techniques with memory alloy. loss of the inherent special properties of NiTi alloy in the Kimura & Sohmura (1988) studied the effects of coating casting process. Titanium is very reactive at high NiTi implants with oxide film to decrease the dissolu- temperatures and the mechanical properties and surface tion of Ni in 1% NaCl solution. The corrosion resistance conditions can be influenced by the mould materials. was measured by anodic polarization measurements; Hamanaka et al. (1985) used graphite coating on phosphate the effect of the oxide film was to suppress dissolution bonded investments in a new casting machine and at low potentials. On repeated polarization, a further observed a noticeable decrease in the reaction between decrease in current density was observed as a result of NiTi alloys and the phosphate bonded investment. stabilization of the passive state on the surface. The The use of NiTi alloy for prefabricated straight-slit oxide film adhered closely to the matrix without peeling type posts was studied by Hasegawa (1989). It appeared or cracking by the plastic deformation associated with that NiTi alloy could be processed without loss of the the shape memory effect. The effect of scratching the shape memory effect by an electric discharge machining oxide surface did not cause dissolution at low potential, and that retention forces after cementing was similar or therefore maintaining a stable surface. stronger with the NiTi trial posts than with other posts. Sachdeva et al. (1990) described the applications of The cementation pressure of the NiTi post into the root shape memory NiTi alloys in dentistry and reported canal filled with unset cement was low. that over 5000 NiTi blade implants had been used on In a later study, Hasegawa (1991) compared differ- patients in Japan. The implant blades were trained to ences in NiTi alloy structure on the influence of stress open at a temperature of 50 °C in order to allow greater on post crown preparations. Threaded posts were con- stability of the implant. After insertion, the implant was structed above the transformation point and were found irrigated by warm saline and, more recently, by an to cause twice as much stress as posts constructed induction coil apparatus. No adverse reports of nickel below that point. At temperatures of 35 °C NiTi posts hypersensitivity have been reported. made of the martensitic structure caused less stress than posts made of the austenite structure. No differences Oral surgery were noted between the two NiTi structures in influencing the thickness of the cement lute. Schettler et al. (1979) investigated the construction of NiTi alloy bone plates to act as alveolar bracing and counteract the effects of mastication during bony repair Construction of implants in the treatment of transverse mandibular fractures. As To take advantage of the shape memory characteristics a result of the shape memory effect, the NiTi alloy of the alloy, NiTi alloy was used for fabrication of endosseous assumed its original shape after repeated deformation blade type implants (Sachdeva et al. 1990). The ability to and produced higher compressive strengths. © 2000 Blackwell Science Ltd International Endodontic Journal, 33, 297–310, 2000 307
    • IEJ339.fm Page 308 Saturday, June 10, 2000 8:50 AM Overview of NiTi alloys Thompson Kuo et al. (1989) described the use of nickel–titanium References alloy in China, for 71 cases of orthopaedic surgery and 265 clinical cases ranging from maxillofacial cor- Andreasen GF, Hilleman TB (1971) An evaluation of 55 cobalt rection to fallopian tube clamping. Nitalloy (56% nickel substituted Nitinol wire for use in orthodontics. Journal of the and 44% titanium, manufactured in Shanghai, China) was American Dental Association 82, 1373–5. compared with Nitinol (55% nickel and 45% titanium Andreasen GF, Morrow RE (1978) Laboratory and clinical from USA) and other materials in common orthopaedic analyses of Nitinol wire. American Journal of Orthodontics 73, use; 316 L stainless steel, Co –Cr–Mo alloy, pure titanium 142 – 51. and Ti6Al4V alloy. Nitalloy showed superior results for Andreasen G, Wass K, Chan KC (1985) A review of superelastic modulus of elasticity, yield and shear strength, elongation and thermodynamic Nitinol wire. Quintessence International ratio and fatigue limit. Miura et al. (1990) described the 9, 623 – 6. Bryant ST, Thompson SA, Al-Omari MAO, Dummer PMH applications of super-elastic NiTi rectangular wire in (1998a) The shaping ability of ProFile rotary nickel–titanium combined surgical– orthodontic treatment. instruments with ISO sized tips in simulated root canals: Part 1. International Endodontic Journal 31, 275–81. Conclusion Bryant S, Thompson SA, Al-Omari MAO, Dummer PMH (1998b) Shaping ability of ProFile rotary nickel–titanium Because of their super-elasticity, nickel–titanium alloys instruments with ISO sized tips in simulated root canals. are being used increasingly in the construction of endo- Part 2. International Endodontic Journal 31, 282–9. dontic instruments. It is important for clinicians to be Buehler WH, Gilfrich JV, Wiley RC (1963) Effect of low temper- aware of the metallurgy of NiTi alloy in order that the ature phase changes on the mechanical properties of alloys near characteristics of instruments constructed from this composition TiNi. Journal of Applied Physics 34, 1475–7. alloy can be appreciated and to encourage research to Buehler WJ, Wang FE (1968) A summary of recent research on the Nitinol alloys and their potential application in ocean maximize their clinical potential. This review attempted engineering. Ocean Engineering 1, 105–20. to highlight the various uses of NiTi alloy in dentistry Buehler WJ, Cross WB (1969) 55-Nitinol unique wire alloy and previous research findings that may have relevance with a memory. Wire Journal 2, 41–9. to endodontology. Burstone CJ, Goldberg AJ (1980) Beta titanium: a new ortho- Whilst NiTi root canal instruments are more flexible dontic alloy. American Journal of Orthodontics 77, 121–32. than stainless steel files and have the ability to prepare Burstone CJ (1981) Variable-modulus orthodontics. American canals quickly and without undue aberrations (Esposito Journal of Orthodontics 80, 1– 16. & Cunningham 1995, Glosson et al. 1995, Thompson & Civian S, Huget EF, Desimon LB (1975) Potential applications Dummer 1997a, 1997b, 1997c, 1997d, 1997e, 1997f, of certain Nickel–Titanium (Nitinol) alloys. Journal of Dental 1998a, 1998b, 1998c, 1998d, Bryant et al. 1998a,b), Research 54, 89 – 96. there are important considerations such as their increased Clinard K, von Fraunhofer JA, Kuftinec MM (1981) The corrosion susceptibility of modern orthodontic spring wires. Journal of cost, the potential decrease in cutting ability due to Dental Research 60A, 628 (Abstract 1277). wear (Walia et al. 1989, Schäfer et al. 1995) and the Drake SR, Wayne DM, Powers JM, Asgar K (1982) Mechanical ability to machine instruments with various designs properties of orthodontic wires in tension, bending and and dimensions to a consistent size (Marsicovetere et al. torsion. American Journal of Orthodontics 82, 206–10. 1996). These issues need to be addressed so that endo- Duerig W (1990) Applications of shape memory. Materials dontists can embrace the use of instruments constructed Science Forum 56 –8, 679 – 92. from this new alloy with confidence. Clearly, the effects Edie J, Andreasen G (1980) Surface corrosion of Nitinol and of sterilization and corrosion during clinical use on NiTi stainless wires. Journal of Dental Research 59A, 528 (Abstract alloys needs to be examined more closely, together with 1037). the enhancement of their hardness by ion implantation Edie JW, Andreasen GF, Zaytoun MP (1981) Surface corrosion (Lee et al. 1996). of Nitinol and stainless steel under clinical conditions. Angle Orthodontics 51, 319 – 24. Esposito PT, Cunningham CJ (1995) A comparison of canal Acknowledgements preparation with nickel–titanium and stainless steel instru- ments. Journal of Endodontics 21, 173–6. Acknowledgement is made to François Aeby, Dentsply, Evans HJ, Durning P (1996) Aligning archwires, the shape of Maillefer Instruments SA, CH-1338 Ballaigues, Switzer- things to come? A fourth and fifth phase of force delivery. land, and to Dr W. J. Evans, Department of Materials Orthodontic Products Update. British Journal of Orthodontics Engineering, University of Wales Swansea. 23, 269 – 75. 308 International Endodontic Journal, 33, 297–310, 2000 © 2000 Blackwell Science Ltd
    • IEJ339.fm Page 309 Saturday, June 10, 2000 8:50 AM Thompson Overview of NiTi alloys Gould JV (1963) Machinability of Nickel–Titanium alloys. Miura F, Mogi M, Okamoto Y (1990) New application of supere- Metcut Research Associates, Report No 573– 4062–1. Office lastic NiTi rectangular wire. Journal of Clinical Orthodontics of Technical Services, U.S. Dept of Commerce, Report No 9, 544 – 8. AD-419009. Saburi T, Tatsumi T, Nenno S (1982) Effects of heat treatment Glosson CR, Haller RH, Brent Dove S, del Rio CE (1995) A on mechanical behaviour of Ti-Ni alloys. Journal of Physics 4, comparison of root canal preparations using NiTi hand, NiTi 261– 6. engine-driven and K-Flex endodontic instruments. Journal of Sachdeva R, Fukuyo S, Suzuki K, Oshida Y, Miyazaki S (1990) Endodontics 21, 146 – 51. Shape memory NiTi alloys – applications in dentistry. Hamanaka H, Doi H, Kohno O, Miura I (1985) Dental castings Materials Science Forum 56-8, 693 – 8. of NiTi alloys. Part 2. New casting techniques for NiTi alloys. Sarkar NK, Redmond W, Schwaninger BM, Goldberg JA (1979) Journal of Dental Materials 4, 573 – 9. The chloride corrosion behaviour of four orthodontic wires. Hasegawa K (1989) The studies on Ti-Ni shape memory alloy Journal of Dental Research 22, 98. for dental use – trial production of prefabricated straight-slit Sarkar NK, Schwaninger B (1980) The in vivo corrosion of Nitinol type posts by electric discharge machining. Journal of Dental wire. Journal of Dental Research 59A, 528 (Abstract 1035). Materials 8, 388– 409. Schäfer E (1997) Root canal instruments for manual use: a Hasegawa K (1991) The studies of Ti-Ni shape memory alloy review. Endodontics and Dental Traumatology 13, 51–64. for dental use – the influence of shape memory alloy post on the Schäfer E, Tepel J, Hoppe W (1995) Properties of endodontic stress of post hole. Journal of Dental Materials 10, 509 –17. hand instruments used in rotary motion. Part 2. Instrumenta- Kapila S, Haugen JW, Watanabe LG (1992) Load-deflection tion of curved canals. Journal of Endodontics 21, 493–7. characteristics of nickel–titanium alloy wires after clinical Schettler D, Baumgart F, Bensmann G, Haasters J (1979) recycling and dry heat sterilisation. American Journal of Method of alveolar bracing in mandibular fractures using Orthodontics and Dentofacial Orthopaedics 102, 120 – 6. a new form of fixation made from memory alloy. Journal Kimura H, Sohmura T (1987) Pure Ti thermal spray coating of Maxillo-Facial Surgery 7, 51– 4. on Ti-Ni shape memory alloys and Ti. Journal of Osaka Serene TP, Adams JD, Saxena A (1995) Nickel–Titanium Instru- University Dental School 6, 672 – 8. ments: Applications in Endodontics. St Louis MO, USA: Ishiyaku Kimura H, Sohmura T (1988) Improvement in corrosion Euro America, Inc. resistance of Ti-Ni shape memory alloy by oxide film coating. Smith GA, von Fraunhofer JA, Casey GR (1992) The effect of Journal of Dental Materials 7, 106 –10. clinical use and sterilisation on selected orthodontic archwires. Kuo P, Yang P, Zhang Y, Yang H, Yu Y, Dai K et al. (1989) The American Journal of Orthodontics and Dentofacial Orthopaedics use of nickel–titanium alloy in orthopaedic surgery in China. 102, 153 – 9. Orthopaedics 12, 111– 6. Stoeckel D, Yu W (1991) Superelastic Ni-Ti wire. Wire Journal Kusy RP, Stush AM (1987) Geometric and material parameters International March, 45 – 50. of a nickel–titanium and a beta titanium orthodontic arch Thompson SA, Dummer PMH (1997a) Shaping ability of wire alloy. Dental Materials 3, 207 –17. Lightspeed rotary nickel–titanium instruments in simulated Kusy RP (1997) A review of contemporary archwires: their root canals. Part 1. Journal of Endodontics 23, 698–702. properties and characteristics. Angle Orthodontist 3, 197 –207. Thompson SA, Dummer PMH (1997b) Shaping ability of Lee JH, Park JB, Andreasen GF, Lakes RS (1988) Thermo- Lightspeed rotary nickel–titanium instruments in simulated mechanical study of NiTi alloys. Journal of Biomedical Materials root canals. Part 2. Journal of Endodontics 23, 742–7. Research 22, 573 – 88. Thompson SA, Dummer PMH (1997c) Shaping ability of Lee D-H, Park JB, Saxena A, Serene TP (1996) Enhanced sur- ProFile .04 Taper Series 29 rotary nickel–titanium instruments face hardness by boron implantation in Nitinol alloy. Journal in simulated root canals. Part 1. International Endodontic of Endodontics 22, 543 – 6. Journal 30, 1– 7. Marsicovetere ES, Clement DJ, del Rio CE (1996) Morphometric Thompson SA, Dummer PMH (1997d) Shaping ability of ProFile video analysis of the engine-driven nickel–titanium Lightspeed 04 Taper Series 29 rotary nickel–titanium instruments instrument system. Journal of Endodontics 22, 231– 5. in simulated root canals. Part 2. International Endodontic Mayhew MJ, Kusy RP (1988) Effects of sterilization on the Journal 30, 8 –15. mechanical properties and the surface topography of nickel– Thompson SA, Dummer PMH (1997e) Shaping ability of NT titanium arch wires. American Journal of Orthodontics and Engine and McXim rotary nickel–titanium instruments Dentofacial Orthopaedics 93, 232 – 6. in simulated root canals. Part 1. International Endodontic Mercier O, Torok E (1982) Mechanical properties of the cold- Journal 30, 262 – 9. worked martensitic NiTi type alloys. Journal de Physique 43, Thompson SA, Dummer PMH (1997f ) Shaping ability of NT 267 – 72. Engine and McXim rotary nickel–titanium instruments Miura F, Mogi M, Ohura Y, Hamanaka H (1986) The super-elastic in simulated root canals. Part 2. International Endodontic property of the Japanese NiTi alloy wire for use in orthodontics. Journal 30, 270 – 8. American Journal of Orthodontics and Dentofacial Orthopaedics Thompson SA, Dummer PMH (1998a) Shaping ability of Mity 90, 1– 10. Roto 360° and Naviflex rotary nickel–titanium instruments © 2000 Blackwell Science Ltd International Endodontic Journal, 33, 297–310, 2000 309
    • IEJ339.fm Page 310 Saturday, June 10, 2000 8:50 AM Overview of NiTi alloys Thompson in simulated root canals. Part 1. Journal of Endodontics 24, Walia H, Brantley WA, Gerstein H (1988) An initial investiga- 128 – 34. tion of the bending and torsional properties of Nitinol root Thompson SA, Dummer PMH (1998b) Shaping ability of Mity canal files. Journal of Endodontics 14, 346–51. Roto 360° and Naviflex rotary nickel–titanium instruments Walia H, Costas J, Brantley W, Gerstein H (1989) Torsional in simulated root canals. Part 2. Journal of Endodontics 24, ductility and cutting efficiency of the Nitinol file. Journal of 135 – 42. Endodontics 15, 174 (Abstract 22). Thompson SA, Dummer PMH (1998c) Shaping ability of Quantec Wang FE, Pickart SJ, Alperin HA (1972) Mechanism of the Series 2000 rotary nickel–titanium instruments in simulated TiNi martensitic transformation and the crystal structures root canals. Part 1. International Endodontic Journal 31, of TiNi-II and TiNi-III phases. Journal of Applied Physics 43, 259 – 67. 97 –112. Thompson SA, Dummer PMH (1998d) Shaping ability of Yoneyama T, Doi H, Hamanaka H, Okamoto Y, Mogi M, Miura Quantec Series 2000 rotary nickel-titanium instruments F (1992) Super-elasticity and thermal behaviour of Ni-Ti in simulated root canals. Part 2. International Endodontic alloy orthodontic arch wires. Journal of Dental Materials 11, Journal 31, 268 – 74. 1– 10. 310 International Endodontic Journal, 33, 297–310, 2000 © 2000 Blackwell Science Ltd